|Publication number||US6921264 B2|
|Application number||US 10/661,692|
|Publication date||Jul 26, 2005|
|Filing date||Sep 12, 2003|
|Priority date||Aug 23, 2002|
|Also published as||CA2496119A1, CA2496119C, CN1688263A, CN100506186C, DE50311713D1, EP1530446A1, EP1530446B1, EP2108331A1, EP2108331B1, EP2108332A1, EP2108333A1, EP2108333B1, EP2108334A1, EP2108334B1, US7008226, US20040038180, US20040053196, WO2004017857A1|
|Publication number||10661692, 661692, US 6921264 B2, US 6921264B2, US-B2-6921264, US6921264 B2, US6921264B2|
|Inventors||Jorg Mayer, Marcel Aeschlimann, Laurent Torriani|
|Original Assignee||Woodwelding Ag|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (99), Non-Patent Citations (4), Referenced by (107), Classifications (48), Legal Events (3)|
|External Links: USPTO, USPTO Assignment, Espacenet|
1. Field of the Invention
The Invention lies in the field of medical technology and relates to an implant that is implanted in human or animal bone tissue or in bone tissue supplemented with bone substitute material.
2. Description of Related Art
The implant according to the invention is, for example, a dental implant that, assuming the function of a natural tooth root, is implanted into a jawbone. In order to permit fastening of an artificial tooth crown, a bridge, or a dental prosthesis, the dental implant comprises, at its proximal end, a fixation location that, after implantation, is located in the region of the bone surface. The dental implant may represent a complete tooth replacement, that is to say may also have a crown region in addition to a root region to be implanted. The implant may also have a different function and may be suitable for implantation in another human or animal bone. Generally speaking, the implant serves for connecting a bone part with another tissue part, in particular with another bone part, or with an artificial part, which artificial part may support or replace a bone part (e.g., artificial joint) or a tooth or it may be a therapeutic auxiliary device (e.g., drug release device, drainage device, or stimulating device for electric or chemical stimulation). The implant may further be such therapeutic auxiliary device itself or it may serve for replacing missing bone tissue or possibly bone tissue to be regenerated (e.g. after removal of a tumor) or it may be an augmentation element for augmenting natural bone in a desired way.
Fixation of tooth replacement structures (individual teeth, groups of teeth, part-prostheses, or complete prostheses) based on the above mentioned dental implants with fixation locations is, according to the state of the art, realized in the following steps: after removal of the natural tooth root one waits until naturally regenerated bone tissue fills the opening in the jawbone. In the region of the regenerated bone tissue an opening adapted to the implant is created. The implant is positioned in the opening, wherein the opening is deep enough for housing the complete implant, which therefore does not protrude beyond the opening. An inner thread defining the fixation location at the proximal face of the implant is closed with a cover screw. The gum is closed over the cover screw and one waits until the bone tissue has ingrown with the implant and by way of this has a stability (secondary stability) sufficient for the loading to be expected. Then; in a further step, the gum is opened over the implant and the cover screw is replaced by a spacer, wherein the spacer projects beyond the gum. Only when the gum around the spacer is healed is the tooth replacement structure fastened on the implant. The briefly described procedure entails a treatment duration of twelve to eighteen months for the patient, of which two to three months fall in the time between the implantation and a point in time at which the bone tissue has grown around the implant or the implant is ingrown in the bone tissue such that the implant has sufficient stability for loading.
The first waiting period (regeneration of bone tissue in an opening in the jawbone) may be avoided or shortened if implants are used which in their shape are adapted as exactly as possible to the original opening, as for example described in the publication U.S. Pat. No. 6,132,214 (Suhonen et al.).
The dental implants according to the state of the art usually consist of pure titanium or of a titanium alloy. These materials exhibit a very good biological compatibility and there are various known surface designs that further improve osseointegration. Very often the implants also comprise macroscopic structures that permit the bone tissue to grow into or through the implant. However, the stability of these known dental implants is only adequate for full loading after complete osseointegration, i.e. only when they are intimately grown around by bone tissue or ingrown or intergrown with bone tissue (secondary stability). In osteoporotic or soft bone, as well as in poorly regenerating bone tissue, for example of older patients it may happen that no sufficient implant stability can be achieved.
The primary stability of the above-described dental implants, i.e. their stability directly after implantation, is greatly limited. For this reason the above mentioned waiting time is added between implantation and further build up. The primary stability of the mentioned implants varies according to implant form, but in most cases it is not sufficient for full loading. Pin-like implants with a thread are restrictedly loadable by tension and compression and possibly transverse forces, in particular when implanted such that at least one thread convolution lies in the region of the cortical part of the bone. They can hardly be loaded by torsion. Implants that do not have a round cross section, i.e. which are adapted to a natural tooth root, are more stable when loaded by torsion, but less stable when loaded by tension. The same applies to plate-like dental implants that may also comprise a plurality of fixation locations.
The un-sufficient loadability of known dental implants would, on loading immediately after implantation lead to movements between implant and bone tissue great enough for impeding or even preventing osseo-integration. However, immediate loading of implants is not only desirable in order to shorten the treatment duration, but also to avoid atrophy of the jawbone due to non-loading, i.e. to promote osseo-integration by way of micro-movements (not exceeding a physiological measure) between implant and bone tissue, which can only be achieved by loading a stable implant.
The primary stability, in particular the ability to be loaded in tension and compression is increased for pin-like implants according to the state of the art by way of a suitably formed threads (U.S. Pat. No. 3,499,222), by spread-out elements (e.g. U.S. Pat. No. 5,766,009, EP-1184006) or by collar-like elements. Anchor-like implants in particular used for fastening wires or sutures are equipped with barb-like surface structures (U.S. Pat. No. 4,360,343) for increasing the primary and secondary stability regarding tension loading. However, these improvements neither permit loading of the implants directly after implantation.
It is therefore the object of the invention to provide an implant suitable for implantation in bone tissue or in bone tissue being supplemented by bone substitute material, which implant has a very good primary stability, such that it is, for instance, able to be loaded immediately after implantation, which implant however is equipped for further clinical functions, e.g. for osseo-integration, for passage of particles or molecules into or out of the implant (delivery or drainage), for electric or chemical stimulation, etc., and this also immediately after implantation. The further clinical functions of the implant are not to suffer clinically relevant restriction by the wanted primary stability. If the implant has a load bearing function, i.e. if it is e.g. a dental implant, it is to be able to be loaded as unlimited as possible immediately after implantation or at least significantly earlier after implantation than known such implants. However, osseo-integration (further clinical function) remains substantially unhindered, i.e. begins immediately after implantation such that the above mentioned positive effects on osseo-integration effected by early loading can be fully exploited. Furthermore, neither the implant according to the invention nor its implantation is to be significantly more complicated than is the case for implants according to the state of the art.
The surfaces of the implant according to the invention, which are to come into contact with bone tissue or which are, for instance, to be grown around by bone tissue or are to be intergrown by bone tissue comprise regions of a first type and regions of a second type different from the surface regions of the first type.
The surface regions of the first type are equipped in a per se known manner for one or more than one predetermined clinical function. Examples of such clinical functions include the promotion or at least enablement of osseointegration for a good secondary stability, delivery of therapeutically effective compounds into tissue surrounding the implant, removal of unwanted compounds from tissue surrounding the implant (drainage), and electric or chemical stimulation of tissue surrounding the implant.
For an implant with a load bearing function, the surface regions of the first type comprise, for example, structures suitable for a stable ingrowth or through growth with vital bone tissue and they are, at least regarding osseo-integration, biologically active. Further or additional compounds having desirable effects, such as osseointegrative, inflammation-suppressing, infection-combating, and growth-promoting effects, may be delivered through the surface regions of the first type or these surfaces may be equipped for passage of therapeutically effective stimulating impulses.
The surface regions of the first type are, for example, biologically compatible surfaces (e.g. made of titanium) and they can be formed to have structures that are suitable for bone. tissue ingrowth. Such surfaces may further be coated with a material comprising calcium phosphate, they may be modified by phosphonates or peptide sequences, for example, and/or they may comprise gels or polymers containing growth factors.
The surface regions of the second type are designed for producing the primary stability. For this purpose these regions comprise a material that can be liquefied by mechanical oscillation, i.e. a material having thermoplastic properties (thermoplast or composite material comprising a thermoplastic component) or a thixotropic cement, wherein the liquefiable material is liquefied and pressed into unevennesses, pores or suitably produced geometries of the bone tissue surrounding the implant by application of mechanical oscillation (e.g. ultrasonic oscillation) during implantation.
The material constituting the surface regions of the second type forms part of the outer surface of the implant already before implantation or it is located on the inside of the implant and during implantation it is pressed in a liquefied state through corresponding openings to the outer surface of the implant, where it creates, in situ, the surface regions of the second type.
For the liquefied material of the surface regions of the second type to be able to be pressed into the bone tissue during implantation, the surface regions of the second type are arranged such that they come into contact with the bone tissue on positioning the implant in the bone. This means that the surface regions of the second type project, for example, at least locally beyond the surface regions of the first type or they are located at implant edges, projections, etc. For implants containing the material forming the surface regions of the second type inside, openings for pressing out the liquefiable material are arranged accordingly.
The surface regions of the two types are arranged and the liquefiable material and/or liquefaction are dimensioned such that the surface regions of the second type remain as free as possible of the liquefied material. This guarantees that the further clinical functions of the first type regions are not hindered or are hindered only to a clinically acceptable degree, even immediately after implantation. Therewith it is achieved that osseo-integration of surface regions of the first type is not only not hindered but is also not delayed and, therefore, starts immediately after implantation.
For implants which during implantation are moved relative to the bone tissue in an implantation direction, separation of the two types of surface regions is achieved by arranging the two types of surface regions next to one another and parallel to the implantation direction.
In the same way as known implants, the implant according to the invention is implanted in an opening specifically created for the implant possibly in beforehand regenerated bone tissue (e.g. of the jawbone) wherein this opening may accommodate the whole implant (root region) or wherein the implant in a self-cutting manner may be forced deeper than the opening into the bone tissue. The opening may, for example, only concern the cortical bone layer or, with a suitable design of the implant, it may be completely omitted. The implant according to the invention may also in the sense of a replica have a shape adapted to an irregular form of a bone cavity, e.g. the shape of a removed, natural tooth root and may be implanted directly into this cavity.
The implant according to the invention is, for example, a dental implant having the shape of a pin or of a natural tooth root and having at its proximal end a fixation location (e.g. pocket hole with an inner thread or location at which the dental surgeon may create such a pocket hole) or an artificial crown region. At its distal end it may be formed chisel-shaped and/or be provided with lateral self-cutting or grooving structures. It may furthermore be plate-shaped, disk-shaped, or blade-shaped and comprise one or more fixation locations, or it may have the shape of an anchor on which for example a wire or a suture can be fastened.
The implant according to the invention is of one piece and comprises the above-defined, different surface regions that, for example, consist of different materials, or it contains the liquefiable material inside and comprises openings through which the material when liquefied is pressed to the outer side of the implant. The implant may also be two-piece or multi-piece, wherein the surgeon combines two or more parts of various materials to form the implant.
For implantation, the implant according to the invention is positioned in the opening in the bone (or bone tissue supplemented with bone substitute material), e.g. in a jawbone, and then mechanical oscillation is applied to it, for example ultrasound, and simultaneously it is pressed against the bone. This causes at least part of the liquefiable material to be liquefied and pressed into pores, surface unevennesses and/or created geometries of the surrounding bone tissue, where after solidification it forms a positive-fit connection between the implant and the surrounding bone tissue or possibly bone substitute material. Depending on the implant design, the implant may also be advanced in the bone tissue (implantation direction) simultaneously to liquefaction.
For applying mechanical oscillation to the positioned implant, the sonotrode of an ultrasound apparatus is placed onto the proximal end of the implant. Experiments show that good results are achieved with a power of 0.2 to 20 W per square millimeters active surface. The frequency of the oscillations is between 2 and 200 kHz.
Implants according to the invention and having a load bearing function (e.g. dental implants) comprise a central implant part carrying the surface regions of the first type and being made of metal (e.g. steel, titanium, cobalt/chromium alloy), of a ceramic or glass-like material (e.g. aluminum oxide, zirconium oxide, ceramic or glass of calcium phosphate), of a thermoset or high-temperature thermoplastic polymers (Polyether arylketones, Polyfluoro- or polychloroethylenes, polyether imides, polyether sulphones, polyvinylchloride, polyurthanes, polysulphones, polyesters) or of a composite material (e.g. high-temperature thermoplast reinforced with carbon fibers). Such implants also comprise a peripheral implant part of the liquefiable material, for example of a material with thermoplastic properties. The liquefiable material may also be placed on the inside of a hollow, central implant part, wherein the walling of the central implant part has through openings through which the liquefied material is pressed under the influence of the mechanical oscillation, in order to form surface regions of the second type on the outside of the walling. The implant parts may be connected to one another on the part of the manufacturer or only be brought into connection with one another by the surgeon directly before or during implantation.
Implants according to the invention which have no relevant load bearing function (e.g. implants having a delivery function, a drainage function, or a stimulating function) may also comprise a central implant part and a peripheral implant part, the peripheral implant part consisting at least partly of the liquefiable material, wherein the mechanical stability (load bearing function), which is necessary for implantation may be taken over by the peripheral implant part, the central implant part having but very little mechanical-stability. Such a central implant part is e.g. a permeable container e.g. of porous calcium phosphate or of an other bone substitute material having little mechanical stability or of a thin membrane, wherein delivery or drainage or simulation takes place through the container wall. The central implant part may also be a body of porous calcium phosphate or of another bone substitute material and have the function of initiating or assisting formation of missing or additionally desired bone tissue. It is possible to provide the liquefiable material on the inside of the central implant part and press it when liquefied through corresponding openings to the outer surface of the central implant part, even if the latter implant part has little mechanical stability.
The implant according to the invention may also consist of only one material that is able at the same time to fulfill the demands with regard to the mechanical strength of the implant and possibly of a fixation location, the demands set by the further clinical functions of the surface regions of the first type (e.g. biological integration or secondary stabilization respectively) and the demand of the liquifiability by mechanical oscillation. As the case may be, in various regions of the implant the one material may be filled to varying degrees (e.g. with fibers, whiskers, or particles) or it may be filled with different materials in different regions. In this case too, a suitable design of the surface regions to be integrated in the bone tissue must ensure that, upon implantation, the surface regions of the second type or the liquefied material respectively comes into contact in particular with the bone tissue and that the liquefied material is not or only to a clinically irrelevant degree carried onto the surface regions of the first type.
For implants with surface regions equipped for osseo-integration, the liquefiable material is advantageously at least partly biologically degradable (resorbable) so that the stability function (primary stability) of the positive fit between the implant and the bone tissue is gradually taken over by the stability function (secondary stability) of the osseo-integration, which advantageously increases to the same degree as the liquefiable material is resorbed, i.e. the primary stability decreases. In particular in the case of osteoporotic bone tissue or poorly regenerating bone tissue it may be advantageous to permanently retain the primary stabilization as a supplement to the secondary stabilization, i.e. to use a non-resorbable, liquefiable material, which may also be equipped for good biological integration (secondary osseointegration).
For implants with other than load bearing functions, the liquefiable material is advantageously at least partly resorbable, if the implant is to be removed from the bone tissue or to be completely replaced by bone tissue. If the primary stability is to be retained, the liquefiable material is not resorbable or only partly resorbable.
Resorbable polymers such as those based on lactic acid and/or glycolic acid (PLA, PLLA, PGA, PLGA etc.) or polyhydroxyalkanoates (PHA), polycaprolactones (PCL), polysaccharides, polydioxanones (PD), polyanhydrides, polypeptides or corresponding copolymers or blended polymers or composite materials containing the mentioned polymers as components are suitable as resorbable liquefiable materials. Thermoplasts such as, for example, polyolefins, polyacrylates, polymetacrylates, polycarbonates, polyamides, polyesters, polyurethanes, polysulphones, polyaryl ketones, polyimides, polyphenyl sulphides or liquid crystal polymers (LCPS), polyacetals, halogenated polymers, in particular halogenated polyoelefins, polyphenylene sulphides, polysulphones, polyethers or corresponding copolymers or blended polymers or composite materials containing the mentioned polymers as components are suitable as non-resorbable polymers. Applicable thixotropic systems are resorbable, partly resorbable, or non-resorbable polymeric, ceramic or hydraulic cements (e.g. Norian® of Synthes or Sulfix® of Centerpulse).
The liquefiable material may contain foreign phases or compounds serving further functions. In particular, the liquefiable material may be strengthened by admixing fibers or whiskers (e.g. of calcium phosphate ceramics or glasses) and such represent a composite material. The liquefiable material may further contain components that expand or dissolve (create pores) in situ (e.g. polyesters, polysaccharides, hydrogels, sodium phosphates) or compounds to be released in situ and having a therapeutic effect for promotion of healing and regeneration (e.g. growth factors, antibiotics, inflammation inhibitors or buffers such as sodium phosphate against adverse effects of acidic decomposition). If the liquefiable material is resorbable, release of such compounds is delayed.
The implant part not comprising the liquefiable material is not resorbable, if the implant is to remain in the patient's body or if it is to be removed surgically. However, this implant part may also be made at least partly of a resorbable material, which after implantation is gradually replaced by vital tissue.
The design of the implant and the selection of the liquefiable material are to be matched to one another such that the strength of the positive fit is sufficient for the expected loading, and such that liquefaction entails a reasonable, that is to say, a low as possible heat release. If liquefiable materials with a relatively high softening temperature are used, it is advantageous to ensure that the implant as a whole (including liquefiable material) conducts the mechanical oscillations as a resonator so that the liquefiable material is liquefied in the surface regions of the second type only very locally, e.g. only in regions of suitably provided energy directors. In this manner the released quantity of heat can be kept to within an acceptable scope. In particular, when using a material with a relatively low softening temperature or a material being liquefiable without release of heat (e.g. thixotropic cements), liquefaction may also be effected in the inside of the liquefiable material (by large damping of the exciting oscillation) or at contact locations between the central and peripheral implant part.
The heat burden on the tissue during implantation may be reduced even further by designing the central implant part to comprise materials with a large heatconducting capability and/or a large thermal capacity (e.g. silicon carbide) and, as the case may be, to comprise cooling channels through which a cooling medium flows.
Exemplary embodiments of the implant according to the invention are described in detail by way of the following Figures, wherein:
The central implant part 1 comprises surface regions 4 of the first type (e.g. with osseo-integrative, inflammation-inhibiting, infection-combating and/or growthpromoting properties) extending parallel to the implantation direction A. Between the surface regions 4 of the first type, the implant comprises surfaces that are suitable for connection to the peripheral implant part 2. The connection between the peripheral implant part 2 and the central implant part may be an adhesive connection 5 (
As seen in
The implant illustrated in
For an implant to be positioned in a deeper opening and not to be displaced or only slightly during oscillation, the surface regions of the first and second type may be arranged differently. The surface regions 8 of the second type may form, instead of fingers 6, a pattern of points or intersecting lines. The arrangement of the surface regions 8 of the second type is thus to be adapted to the manner of implantation. Furthermore, the arrangement of the second type surface regions is to be adapted to the primary stability to be achieved by the liquefied material, i.e. the primary stability that cannot be achieved by the implant shape.
The two implant parts 1 and 2 of the implants shown in
The advantage of the joining-together by the surgeon lies in the fact that the two parts can be sterilized separately, i.e. possibly using different methods being adapted to the various functionalities of the parts. Sterilization of the whole implant is then not necessary. The joining-together just before implantation allows the manufacturer to make available a set of central implant parts differing from one another. For example, the central implant parts may vary with respect to length and diameter and peripheral implant parts differing for example with respect to material or finger thickness, so that the surgeon may himself put together a suitable implant exactly for the case in question (greater variability at lower number of components).
For implanting the pin-shaped implants according to
The body part 1.2 according to
The implant according to
The body part 1.2 according to
Implants according to
The design of the anchor edges as cutter blades simplifies implantation without the use of a suitable opening in the bone tissue or in an opening that only concerns the cortical bone.
The plate-, disk- or blade-shaped dental implants of which one example is shown in
Plate-, disk- or blade-shaped implants are not applicable only in the dental field but also in the orthopedic field, for which they comprise suitably equipped proximal regions.
If the central implant part 1 is provided with a chisel-like, distal end, as shown, the implant according to
In an implant according to
The liquefiable material which is provided in the inner space 2′ of the central implant part may be a thermoplastic material like liquefiable material arranged on the outside of a central implant part. Advantageously, however, the liquefiable material is a polymer or hydraulic cement having thixotropic properties, which cement is curable after implantation by, for example, ultraviolet light, heat, mechanical oscillations or simply with time.
When using a thermoplast as a liquefiable material being provided in an inner space 2′ of the central implant part, energy directors may have to be arranged on the inner surfaces of the central implant part 1 or on the surfaces of the thermoplast.
The liquefiable material of the implant according to
The peripheral implant part consists at least partly of the liquefiable material (surface regions 8 of the second type) and is designed as a cage having sufficient stability for implantation. The central implant part, which does not have any load bearing function, is arranged inside the cage. The implant is positioned in a bone cavity and the oscillation energy is applied to the implant it by a device (sonotrode of an ultrasound device) that is adapted to the proximal face of the implant. The sonotrode to be used for the implant according to
The central implant part constituting the surface regions 4 of the first type of the implant according to
The cage according to
The peripheral implant part 2 is in the embodiment according to
The implant according to
The implant according to
The implants according to
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|U.S. Classification||433/173, 433/174|
|International Classification||A61F2/02, A61B17/68, A61F2/00, A61B17/70, A61C8/00, A61L27/00, A61F2/44, A61F2/46, A61F2/30, A61F2/28|
|Cooperative Classification||A61C8/0019, A61C8/0018, A61F2002/30088, A61F2002/30892, A61C8/0012, A61F2002/4475, A61F2/4611, A61F2002/30064, A61F2002/30032, A61F2/0077, A61F2210/0004, A61F2250/003, A61F2/30767, A61F2210/008, A61F2002/4683, A61F2002/30784, A61F2002/30067, A61L2430/02, A61B17/70, A61B17/68, A61F2210/0071, A61F2002/30899, A61F2002/30884, A61F2002/30065, A61F2/447, A61C8/0016, A61F2002/4627, A61F2002/30878, A61B2017/00955, A61F2002/30062|
|European Classification||A61C8/00E3, A61B17/70, A61C8/00E, A61B17/68, A61F2/44F6, A61F2/46B7|
|Nov 11, 2003||AS||Assignment|
Owner name: WOODWELDING AG, SWITZERLAND
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:MAYER, JORG;AESCHLIMANN, MARCEL;TORRIANI, LAURENT;REEL/FRAME:014120/0233
Effective date: 20031027
|Jan 22, 2009||FPAY||Fee payment|
Year of fee payment: 4
|Jan 17, 2013||FPAY||Fee payment|
Year of fee payment: 8